Decellularization and recellularization of solid organs

ABSTRACT

The invention provides for methods and materials to decellularize a solid organ and to recellularize such a decellularized organ to thereby generate a solid organ.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.13/725,030, filed Dec. 21, 2012, which is a continuation of U.S. patentapplication Ser. No. 12/064,613, filed Oct. 27, 2008, which is aNational Stage application under 35 U.S.C. § 371 and claims benefitunder 35 U.S.C. § 119(a) of International Application No.PCT/US2006/033415 having an International Filing Date of Aug. 28, 2006,which claims the benefit of priority of U.S. Application No. 60/815,242having a filing date of Jun. 19, 2006 and U.S. Application No.60/711,501 having a filing date of Aug. 26, 2005.

TECHNICAL FIELD

This invention relates to organs and tissues, and more particularly tomethods and materials for decellularizing and recellularizing organs andtissues.

BACKGROUND

Biologically derived matrices have been developed for tissue engineeringand regeneration. The matrices developed to date, however, generallyhave a compromised matrix structure and/or do not exhibit a vascular bedthat allows for effective reconstitution of the organ or tissue. Thisdisclosure describes methods for decellularization and recellularizationof organs and tissues.

SUMMARY

The invention provides for methods and materials to decellularize anorgan or tissue as well as methods and materials to recellularize adecellularized organ or tissue.

In one aspect, the invention provides for a decellularized mammalianheart. A decellularized mammalian heart includes a decellularizedextracellular matrix of the heart that has an exterior surface. Theextracellular matrix of a decellularized heart substantially retains themorphology of the extracellular matrix prior to decellularization, andthe exterior surface of the extracellular matrix is substantiallyintact.

Representative hearts include but are not limited to rodent hearts, pighearts, rabbit hearts, bovine hearts, sheep hearts, or canine hearts.Another representative heart is a human heart. The decellularized heartcan be cadaveric. In some embodiment, the decellularized heart is aportion of an entire heart. For example, a portion of an entire heartcan include, without limitation, a cardiac patch, an aortic valve, amitral valve, a pulmonary valve, a tricuspid valve, a right atrium, aleft atrium, a right ventricle, a left ventricle, septum, coronaryvasculature, a pulmonary artery, or a pulmonary vein.

In another aspect, the invention provides for a solid organ. A solidorgan as described herein includes the decellularized heart describedabove and a population of regenerative cells attached thereto. In someembodiments, the regenerative cells are pluripotent cells. In someembodiment, the regenerative cells are embryonic stem cells, umbilicalcord cells, adult-derived stem or progenitor cells, bone marrow-derivedcells, blood-derived cells, mesenchymal stem cells (MSC), skeletalmuscle-derived cells, multipotent adult progenitor cells (MAPC), cardiacstem cells (CSC), or multipotent adult cardiac-derived stem cells. Insome embodiments, the regenerative cells are cardiac fibroblasts,cardiac microvasculature cells, or aortic endothelial cells.

Generally, the number of the regenerative cells attached to thedecellularized heart is at least about 1,000. In some embodiments, thenumber of the regenerative cells attached to the decellularized heart isabout 1,000 cells/mg tissue (wet weight; i.e., pre-decellularizedweight) to about 10,000,000 cells/mg tissue (wet weight). In someembodiments, the regenerative cells are heterologous to thedecellularized heart. Also in some embodiments, the solid organ is to betransplanted into a patient and the regenerative cells are autologous tothe patient.

In yet another aspect, the invention provides a method of making a solidorgan. Such a method generally includes providing a decellularized heartas described herein, and contacting the decellularized heart with apopulation of regenerative cells under conditions in which theregenerative cells engraft, multiply and/or differentiate within and onthe decellularized heart. In one embodiment, the regenerative cells areinjected or perfused into the decellularized heart.

In still another aspect, the invention provides for a method ofdecellularizing a heart. Such a method includes providing a heart,cannulating the heart at one or more than one cavity, vessel, and/orduct to produce a cannulated heart, and perfusing the cannulated heartwith a first cellular disruption medium via the one or more than onecannulations. For example, the perfusion can be multi-directional fromeach cannulated cavity, vessel, and/or duct. Typically, the cellulardisruption medium comprises at least one detergent such as SDS, PEG, orTriton X.

Such a method also can include perfusing the cannulated heart with asecond cellular disruption medium via the more than one cannulations.Generally, the first cellular disruption medium can be an anionicdetergent such as SDS and the second cellular disruption medium can bean ionic detergent such as Triton X. In such methods, the perfusing canbe for about 2 to 12 hours per gram (wet weight) of heart tissue.

Unless otherwise defined, all technical and scientific terms used hereinhave the same meaning as commonly understood by one of ordinary skill inthe art to which this invention belongs. Although methods and materialssimilar or equivalent to those described herein can be used in thepractice or testing of the present invention, suitable methods andmaterials are described below. In addition, the materials, methods, andexamples are illustrative only and not intended to be limiting. Allpublications, patent applications, patents, and other referencesmentioned herein are incorporated by reference in their entirety. Incase of conflict, the present specification, including definitions, willcontrol.

The details of one or more embodiments of the invention are set forth inthe accompanying drawings and the description below. Other features,objects, and advantages of the invention will be apparent from thedrawings and detailed description, and from the claims.

DESCRIPTION OF DRAWINGS

FIG. 1 is a schematic showing the initial preparation for thedecellularization of a heart. The aorta, pulmonary artery, and superiorcaval vein are cannulated (A, B, C, respectively), and the inferiorcaval vein, brachiocephalic artery, left common carotid artery, and leftsubclavian artery are ligated. Arrows indicate the direction ofperfusion in antegrade and retrograde.

FIG. 2 is a schematic of one embodiment of adecellularization/recellularization apparatus.

Like reference symbols in the various drawings indicate like elements.

DETAILED DESCRIPTION

Solid organs generally have three main components, the extracellularmatrix (ECM), cells embedded therein, and a vasculature bed.Decellularization of a solid organ as described herein removes most orall of the cellular components while substantially preserving theextracellular matrix (ECM) and the vasculature bed. A decellularizedsolid organ then can be used as a scaffold for recellularization.Mammals from which solid organs can be obtained include, withoutlimitation, rodents, pigs, rabbits, cattle, sheep, dogs, and humans.Organs and tissues used in the methods described herein can becadaveric.

Solid organs as referred to herein include, without limitation, heart,liver, lungs, skeletal muscles, brain, pancreas, spleen, kidneys,uterus, and bladder. A solid organ as used herein refers to an organthat has a “substantially closed” vasculature system. A “substantiallyclosed” vasculature system with respect to an organ means that, uponperfusion with a liquid, the majority of the liquid is contained withinthe solid organ and does not leak out of the solid organ, assuming themajor vessels are cannulated, ligated, or otherwise restricted. Despitehaving a “substantially closed” vasculature system, many of the solidorgans listed above have defined “entrance” and “exit” vessels which areuseful for introducing and moving the liquid throughout the organ duringperfusion.

In addition to the solid organs described above, other types ofvascularized organs or tissues such as, for example, all or portions ofjoints (e.g., knees, shoulders, or hips), trachea, or spinal cord can bedecellularized using the methods disclosed herein. Further, the methodsdisclosed herein also can be used to decellularize avascular tissuessuch as, for example, cartilage or cornea.

A decellularized organ or tissue as described herein (e.g., heart orliver) or any portion thereof (e.g., an aortic valve, a mitral valve, apulmonary valve, a tricuspid valve, a pulmonary vein, a pulmonaryartery, coronary vasculature, septum, a right atrium, a left atrium, aright ventricle, or a left ventricle), with or withoutrecellularization, can be used for transplanting into a patient.Alternatively, a recellularized organ or tissue as described herein canbe used to examine, for example, cells undergoing differentiation and/orthe cellular organization of an organ or tissue.

Decellularization of Organs or Tissues

The invention provides for methods and materials to decellularize amammalian organ or tissue. The initial step in decellularizing an organor tissue is to cannulate the organ or tissue, if possible. The vessels,ducts, and/or cavities of an organ or tissue can be cannulated usingmethods and materials known in the art. The next step in decellularizingan organ or tissue is to perfuse the cannulated organ or tissue with acellular disruption medium. Perfusion through an organ can bemulti-directional (e.g., antegrade and retrograde). Langendorffperfusion of a heart is routine in the art, as is physiologicalperfusion (also known as four chamber working mode perfusion). See, forexample, Dehnert, The Isolated Perfused Warm-Blooded Heart According toLangendorff, In Methods in Experimental Physiology and Pharmacology:Biological Measurement Techniques V. Biomesstechnik-Verlag March GmbH,West Germany, 1988. Briefly, for Langendorff perfusion, the aorta iscannulated and attached to a reservoir containing cellular disruptionmedium. A cellular disruption medium can be delivered in a retrogradedirection down the aorta either at a constant flow rate delivered, forexample, by an infusion or roller pump or by a constant hydrostaticpressure. In both instances, the aortic valves are forced shut and theperfusion fluid is directed into the coronary ostia (thereby perfusingthe entire ventricular mass of the heart), which then drains into theright atrium via the coronary sinus. For working mode perfusion, asecond cannula is connected to the left atrium and perfusion can bechanged from retrograde to antegrade.

Methods are known in the art for perfusing other organ or tissues. Byway of example, the following references describe the perfusion of lung,liver, kidney, brain, and limbs. Van Putte et al., 2002, Ann. Thorac.Surg., 74(3):893-8; den Butter et al., 1995, Transpl. Int., 8:466-71;Firth et al., 1989, Clin. Sci. (Lond.), 77(6):657-61; Mazzetti et al.,2004, Brain Res., 999(1):81-90; Wagner et al., 2003, J. Artif. Organs,6(3):183-91.

One or more cellular disruption media can be used to decellularize anorgan or tissue. A cellular disruption medium generally includes atleast one detergent such as SDS, PEG, or Triton X. A cellular disruptionmedium can include water such that the medium is osmoticallyincompatible with the cells. Alternatively, a cellular disruption mediumcan include a buffer (e.g., PBS) for osmotic compatibility with thecells. Cellular disruption media also can include enzymes such as,without limitation, one or more collagenases, one or more dispases, oneor more DNases, or a protease such as trypsin. In some instances,cellular disruption media also or alternatively can include inhibitorsof one or more enzymes (e.g., protease inhibitors, nuclease inhibitors,and/or collegenase inhibitors).

In certain embodiments, a cannulated organ or tissue can be perfusedsequentially with two different cellular disruption media. For example,the first cellular disruption medium can include an anionic detergentsuch as SDS and the second cellular disruption medium can include anionic detergent such as Triton X. Following perfusion with at least onecellular disruption medium, a cannulated organ or tissue can beperfused, for example, with wash solutions and/or solutions containingone or more enzymes such as those disclosed herein. Alternating thedirection of perfusion (e.g., antegrade and retrograde) can help toeffectively decellularize the entire organ or tissue. Decellularizationas described herein essentially decellularizes the organ from the insideout, resulting in very little damage to the ECM. An organ or tissue canbe decellularized at a suitable temperature between 4 and 40° C.Depending upon the size and weight of an organ or tissue and theparticular detergent(s) and concentration of detergent(s) in thecellular disruption medium, an organ or tissue generally is perfusedfrom about 2 to about 12 hours per gram of solid organ or tissue withcellular disruption medium. Including washes, an organ may be perfusedfor up to about 12 to about 72 hours per gram of tissue. Perfusiongenerally is adjusted to physiologic conditions including pulsatileflow, rate and pressure.

As indicated herein, a decellularized organ or tissue consistsessentially of the extracellular matrix (ECM) component of all or mostregions of the organ or tissue, including ECM components of the vasculartree. ECM components can include any or all of the following:fibronectin, fibrillin, laminin, elastin, members of the collagen family(e.g., collagen I, III, and IV), glycosaminoglycans, ground substance,reticular fibers and thrombospondin, which can remain organized asdefined structures such as the basal lamina. Successfuldecellularization is defined as the absence of detectable myofilaments,endothelial cells, smooth muscle cells, and nuclei in histologicsections using standard histological staining procedures. Preferably,but not necessarily, residual cell debris also has been removed from thedecellularized organ or tissue.

To effectively recellularize and generate an organ or tissue, it isimportant that the morphology and the architecture of the ECM bemaintained (i.e., remain substantially intact) during and following theprocess of decellularization. “Morphology” as used herein refers to theoverall shape of the organ or tissue or of the ECM, while “architecture”as used herein refers to the exterior surface, the interior surface, andthe ECM therebetween.

The morphology and architecture of the ECM can be examined visuallyand/or histologically. For example, the basal lamina on the exteriorsurface of a solid organ or within the vasculature of an organ or tissueshould not be removed or significantly damaged due to decellularization.In addition, the fibrils of the ECM should be similar to orsignificantly unchanged from that of an organ or tissue that has notbeen decellularized.

One or more compounds can be applied in or on a decellularized organ ortissue to, for example, preserve the decellularized organ, or to preparethe decellularized organ or tissue for recellularization and/or toassist or stimulate cells during the recellularization process. Suchcompounds include, but are not limited to, one or more growth factors(e.g., VEGF, DKK-1, FGF, BMP-1, BMP-4, SDF-1, IGF, and HGF), immunemodulating agents (e.g., cytokines, glucocorticoids, IL2R antagonist,leucotriene antagonists), and/or factors that modify the coagulationcascade (e.g., aspirin, heparin-binding proteins, and heparin). Inaddition, a decellularized organ or tissue can be further treated with,for example, irradiation (e.g., UV, gamma) to reduce or eliminate thepresence of any type of microorganism remaining on or in adecellularized organ or tissue.

Recellularization of Organs or Tissues

The invention provides for materials and methods for generating an organor tissue. An organ or tissue can be generated by contacting adecellularized organ or tissue as described herein with a population ofregenerative cells. Regenerative cells as used herein are any cells usedto recellularize a decellularized organ or tissue. Regenerative cellscan be totipotent cells, pluripotent cells, or multipotent cells, andcan be uncommitted or committed. Regenerative cells also can besingle-lineage cells. In addition, regenerative cells can beundifferentiated cells, partially differentiated cells, or fullydifferentiated cells. Regenerative cells as used herein includeembryonic stem cells (as defined by the National Institute of Health(NIH); see, for example, the Glossary at stemcells.nih.gov on the WorldWide Web). Regenerative cells also include progenitor cells, precursorcells, and “adult”-derived stem cells including umbilical cord cells andfetal stem cells.

Examples of regenerative cells that can be used to recellularize anorgan or tissue include, without limitation, embryonic stem cells,umbilical cord blood cells, tissue-derived stem or progenitor cells,bone marrow-derived step or progenitor cells, blood-derived stem orprogenitor cells, mesenchymal stem cells (MSC), skeletal muscle-derivedcells, or multipotent adult progentitor cells (MAPC). Additionalregenerative cells that can be used include cardiac stem cells (CSC),multipotent adult cardiac-derived stem cells, cardiac fibroblasts,cardiac microvasculature endothelial cells, or aortic endothelial cells.Bone marrow-derived stem cells such as bone marrow mononuclear cells(BM-MNC), endothelial or vascular stem or progenitor cells, andperipheral blood-derived stem cells such as endothelial progenitor cells(EPC) also can be used as regenerative cells.

The number of regenerative cells that is introduced into and onto adecellularized organ in order to generate an organ or tissue isdependent on both the organ (e.g., which organ, the size and weight ofthe organ) or tissue and the type and developmental stage of theregenerative cells. Different types of cells may have differenttendencies as to the population density those cells will reach.Similarly, different organ or tissues may be cellularized at differentdensities. By way of example, a decellularized organ or tissue can be“seeded” with at least about 1,000 (e.g., at least 10,000, 100,000,1,000,000, 10,000,000, or 100,000,000) regenerative cells; or can havefrom about 1,000 cells/mg tissue (wet weight, i.e., prior todecellularization) to about 10,000,000 cells/mg tissue (wet weight)attached thereto.

Regenerative cells can be introduced (“seeded”) into a decellularizedorgan or tissue by injection into one or more locations. In addition,more than one type of cell (i.e., a cocktail of cells) can be introducedinto a decellularized organ or tissue. For example, a cocktail of cellscan be injected at multiple positions in a decellularized organ ortissue or different cell types can be injected into different portionsof a decellularized organ or tissue. Alternatively, or in addition toinjection, regenerative cells or a cocktail of cells can be introducedby perfusion into a cannulated decellularized organ or tissue. Forexample, regenerative cells can be perfused into a decellularized organusing a perfusion medium, which can then be changed to an expansionand/or differentiation medium to induce growth and/or differentiation ofthe regenerative cells.

During recellularization, an organ or tissue is maintained underconditions in which at least some of the regenerative cells can multiplyand/or differentiate within and on the decellularized organ or tissue.Those conditions include, without limitation, the appropriatetemperature and/or pressure, electrical and/or mechanical activity,force, the appropriate amounts of O₂ and/or CO₂, an appropriate amountof humidity, and sterile or near-sterile conditions. Duringrecellularization, the decellularized organ or tissue and theregenerative cells attached thereto are maintained in a suitableenvironment. For example, the regenerative cells may require anutritional supplement (e.g., nutrients and/or a carbon source such asglucose), exogenous hormones or growth factors, and/or a particular pH.

Regenerative cells can be allogeneic to a decellularized organ or tissue(e.g., a human decellularized organ or tissue seeded with humanregenerative cells), or regenerative cells can be xenogeneic to adecellularized organ or tissue (e.g., a pig decellularized organ ortissue seeded with human regenerative cells). “Allogeneic” as usedherein refers to cells obtained from the same species as that from whichthe organ or tissue originated (e.g., related or unrelated individuals),while “xenogeneic” as used herein refers to cells obtained from aspecies different than that from which the organ or tissue originated.

In some instances, an organ or tissue generated by the methods describedherein is to be transplanted into a patient. In those cases, theregenerative cells used to recellularize a decellularized organ ortissue can be obtained from the patient such that the regenerative cellsare “autologous” to the patient. Regenerative cells from a patient canbe obtained from, for example, blood, bone marrow, tissues, or organs atdifferent stages of life (e.g., prenatally, neonatally or perinatally,during adolescence, or as an adult) using methods known in the art.Alternatively, regenerative cells used to recellularize a decellularizedorgan or tissue can be syngeneic (i.e., from an identical twin) to thepatient, regenerative cells can be human lymphocyte antigen(HLA)-matched cells from, for example, a relative of the patient or anHLA-matched individual unrelated to the patient, or regenerative cellscan be allogeneic to the patient from, for example, a non-HLA-matcheddonor.

Irrespective of the source of the regenerative cells (e.g., autologousor not), the decellularized solid organ can be autologous, allogeneic orxenogeneic to a patient.

In certain instances, a decellularized organ may be recellularized withcells in vivo (e.g., after the organ or tissue has been transplantedinto an individual). In vivo recellularization may be performed asdescribed above (e.g., injection and/or perfusion) with, for example,any of the regenerative cells described herein. Alternatively oradditionally, in vivo seeding of a decellularized organ or tissue withendogenous cells may occur naturally or be mediated by factors deliveredto the recellularized tissue.

The progress of regenerative cells can be monitored duringrecellularization. For example, the number of cells on or in an organ ortissue can be evaluated by taking a biopsy at one or more time pointsduring recellularization. In addition, the amount of differentiationthat regenerative cells have undergone can be monitored by determiningwhether or not various markers are present in a cell or a population ofcells. Markers associated with different cells types and differentstages of differentiation for those cell types are known in the art, andcan be readily detected using antibodies and standard immunoassays. See,for example, Current Protocols in Immunology, 2005, Coligan et al.,Eds., John Wiley & Sons, Chapters 3 and 11. Nucleic acid assays as wellas morphological and/or histological evaluation can be used to monitorrecellularization.

Controlled System for Decellularizing and/or Recellularizing an Organ orTissue

The invention also provides for a system (e.g., a bioreactor) fordecellularizing and/or recellularizing an organ or tissue. Such a systemgenerally includes at least one cannulation device for cannulating anorgan or tissue, a perfusion apparatus for perfusing the organ or tissuethrough the cannula(s), and means (e.g., a containment system) tomaintain a sterile environment for the organ or tissue. Cannulation andperfusion are well-known techniques in the art. A cannulation devicegenerally includes size-appropriate hollow tubing for introducing into avessel, duct, and/or cavity of an organ or tissue. Typically, one ormore vessels, ducts, and/or cavities are cannulated in an organ. Aperfusion apparatus can include a holding container for the liquid(e.g., a cellular disruption medium) and a mechanism for moving theliquid through the organ (e.g., a pump, air pressure, gravity) via theone or more cannulae. The sterility of an organ or tissue duringdecellularization and/or recellularization can be maintained using avariety of techniques known in the art such as controlling and filteringthe air flow and/or perfusing with, for example, antibiotics,anti-fungals or other anti-microbials to prevent the growth of unwantedmicroorganisms.

A system to decellularize and recellularize organ or tissues asdescribed herein can possess the ability to monitor certain perfusioncharacteristics (e.g., pressure, volume, flow pattern, temperature,gases, pH), mechanical forces (e.g., ventricular wall motion andstress), and electrical stimulation (e.g., pacing). As the coronaryvascular bed changes over the course of decellularization andrecellularization (e.g. vascular resistance, volume), apressure-regulated perfusion apparatus is advantageous to avoid largefluctuations. The effectiveness of perfusion can be evaluated in theeffluent and in tissue sections. Perfusion volume, flow pattern,temperature, partial O₂ and CO₂ pressures and pH can be monitored usingstandard methods.

Sensors can be used to monitor the system (e.g., bioreactor) and/or theorgan or tissue. Sonomicromentry, micromanometry, and/or conductancemeasurements can be used to acquire pressure-volume or preloadrecruitable stroke work information relative to myocardial wall motionand performance. For example, sensors can be used to monitor thepressure of a liquid moving through a cannulated organ or tissue; theambient temperature in the system and/or the temperature of the organ ortissue; the pH and/or the rate of flow of a liquid moving through thecannulated organ or tissue; and/or the biological activity of arecellularizing organ or tissue. In addition to having sensors formonitoring such features, a system for decellularizing and/orrecellularizing an organ or tissue also can include means formaintaining or adjusting such features. Means for maintaining oradjusting such features can include components such as a thermometer, athermostat, electrodes, pressure sensors, overflow valves, valves forchanging the rate of flow of a liquid, valves for opening and closingfluid connections to solutions used for changing the pH of a solution, aballoon, an external pacemaker, and/or a compliance chamber. To helpensure stable conditions (e.g., temperature), the chambers, reservoirsand tubings can be water-jacketed.

It can be advantageous during recellularization to place a mechanicalload on the organ and the cells attached thereto. As an example, aballoon inserted into the left ventricle via the left atrium can be usedto place mechanical stress on a heart. A piston pump that allowsadjustment of volume and rate can be connected to the balloon tosimulate left ventricular wall motion and stress. To monitor wall motionand stress, left ventricular wall motion and pressure can be measuredusing micromanometry and/or sonomicrometry. In some embodiments, anexternal pacemaker can be connected to a piston pump to providesynchronized stimulation with each deflation of the ventricular balloon(which is equivalent to the systole). Peripheral ECG can be recordedfrom the heart surface to allow for the adjustment of pacing voltage,the monitoring of de- and repolarization, and to provide a simplifiedsurface map of the recellularizing or recellularized heart.

Mechanical ventricular distention can also be achieved by attaching aperistaltic pump to a canula inserted into the left ventricle throughthe left atrium. Similar to the procedure described above involving aballoon, ventricular distention achieved by periodic fluid movement(e.g., pulsatile flow) through the canula can be synchronized withelectrical stimulation.

Using the methods and materials disclosed herein, a mammalian heart canbe decellularized and recellularized and, when maintained under theappropriate conditions, a functional heart that undergoes contractilefunction and responds to pacing stimuli and/or pharmacologic agents canbe generated. This recellularized functional heart can be transplantedinto a mammal and function for a period of time.

FIG. 2 shows one embodiment of a system for decellularizing and/orrecellularizing an organ or tissue (e.g., a bioreactor). The embodimentshown is a bioreactor for decellularizing and recellularizing a heart.This embodiment has an adjustable rate and volume peristaltic pump (A);an adjustable rate and volume piston pump connected to anintraventricular balloon (B); an adjustable voltage, frequency andamplitude external pacemaker (C); an ECG recorder (D); a pressure sensorin the ‘arterial line’ (which equals coronary artery pressure) (E); apressure sensor in the ‘venous’ line (which equals coronary sinuspressure) (F); and synchronization between the pacemaker and the pistonpump (G).

A system for generating an organ or tissue can be controlled by acomputer-readable storage medium in combination with a programmableprocessor (e.g., a computer-readable storage medium as used herein hasinstructions stored thereon for causing a programmable processor toperform particular steps). For example, such a storage medium, incombination with a programmable processor, can receive and processinformation from one or more of the sensors. Such a storage medium inconjunction with a programmable processor also can transmit informationand instructions back to the bioreactor and/or the organ or tissue.

An organ or tissue undergoing recellularization can be monitored forbiological activity. The biological activity can be that of the organ ortissue itself such as electrical activity, mechanical activity,mechanical pressure, contractility, and/or wall stress of the organ ortissue. In addition, the biological activity of the cells attached tothe organ or tissue can be monitored, for example, for iontransport/exchange activity, cell division, and/or cell viability. See,for example, Laboratory Textbook of Anatomy and Physiology (2001, Wood,Prentice Hall) and Current Protocols in Cell Biology (2001, Bonifacinoet al., Eds, John Wiley & Sons). As discussed above, it may be useful tosimulate an active load on an organ during recellularization. Acomputer-readable storage medium of the invention, in combination with aprogrammable processor, can be used to coordinate the componentsnecessary to monitor and maintain an active load on an organ or tissue.

In one embodiment, the weight of an organ or tissue can be entered intoa computer-readable storage medium as described herein, which, incombination with a programmable processor, can calculate exposure timesand perfusion pressures for that particular organ or tissue. Such astorage medium can record preload and afterload (the pressure before andafter perfusion, respectively) and the rate of flow. In this embodiment,for example, a computer-readable storage medium in combination with aprogrammable processor can adjust the perfusion pressure, the directionof perfusion, and/or the type of perfusion solution via one or morepumps and/or valve controls.

In accordance with the present invention, there may be employedconventional molecular biology, microbiology, biochemical, and cellbiology techniques within the skill of the art. Such techniques areexplained fully in the literature. The invention will be furtherdescribed in the following examples, which do not limit the scope of theinvention described in the claims.

EXAMPLES Section A. Decellularization (Part I) Example 1—Preparation ofa Solid Organ for Decellularization

To avoid the formation of post mortal thrombi, a donor rat wassystemically heparinized with 400 U of heparin/kg of donor. Followingheparinization, the heart and the adjacent large vessels were carefullyremoved.

The heart was placed in a physiologic saline solution (0.9%) containingheparin (2000 U/ml) and held at 5° C. until further processing. Understerile conditions, the connective tissue was removed from the heart andthe large vessels. The inferior venae cava and the left and rightpulmonary veins were ligated distal from the right and left atrium usingmonofil, non-resorbable ligatures.

Example 2—Cannulation and Perfusion of a Solid Organ

The heart was mounted on a decellularization apparatus for perfusion(FIG. 1). The descending thoracic artery was cannulated to allowretrograde coronary perfusion (FIG. 1, Cannula A). The branches of thethoracic artery (e.g., brachiocephalic trunc, left common carotidartery, left subclavian artery) were ligated. The pulmonary artery wascannulated before its division into the left and right pulmonary artery(FIG. 1, Cannula B). The superior vena cava was cannulated (FIG. 1,Cannula C). This configuration allows for both retrograde and antegradecoronary perfusion.

When positive pressure was applied to the aortic cannula (A), perfusionoccurred from the coronary arteries through the capillary bed to thecoronary venous system to the right atrium and the superior caval vein(C). When positive pressure was applied to the superior caval veincannula (C), perfusion occurred from the right atrium, the coronarysinus, and the coronary veins through the capillary bed to the coronaryarteries and the aortic cannula (A).

Example 3—Decellularization

After the heart was mounted on the decellularization apparatus,antegrade perfusion was started with cold, heparinized, calcium-freephosphate buffered solution containing 1-5 mmol adenosine per Lperfusate to reestablish constant coronary flow. Coronary flow wasassessed by measuring the coronary perfusion pressure and the flow, andcalculating coronary resistance. After 15 minutes of stable coronaryflow, the detergent-based decellularization process was initiated.

The details of the procedures are described below. Briefly, however, aheart was perfused antegradely with a detergent. After perfusion, theheart can be flushed with a buffer (e.g., PBS) retrogradely. The heartthen was perfused with PBS containing antibiotics and then PBScontaining DNase I. The heart then was perfused with 1% benzalkoniumchloride to reduce microbial contamination and to prevent futuremicrobial contamination, and then perfused with PBS to wash the organ ofany residual cellular components, enzymes, or detergent.

Example 4—Decellularization of Cadaveric Rat Hearts

Hearts were isolated from 8 male nude rats (250-300 g). Immediatelyafter dissection, the aortic arch was cannulated and the hearts wereretrogradely perfused with the indicated detergent. The four differentdetergent-based decellularization protocols (see below) were comparedwith respect to their feasibility and efficacy in (a) removing cellularcomponents and (b) preserving vascular structures.

Decellularization generally included the following steps: stabilizationof the solid organ, decellularization of the solid organ, renaturationand/or neutralization of the solid organ, washing the solid organ,degradation of any DNA remaining on the organ, disinfection of theorgan, and homeostasis of the organ.

A) Decellularization Protocol #1 (PEG)

Hearts were washed in 200 ml PBS containing 100 U/ml penicillin, 0.1mg/ml Streptomycin, and 0.25 μg/ml Amphotericin B with no recirculation.Hearts were then decellularized with 35 ml polyethyleneglycol (PEG; 1g/ml) for up to 30 minutes with manual recirculation. The organ was thenwashed with 500 ml PBS for up to 24 hours using a pump forrecirculation. The washing step was repeated at least twice for at least24 hours each time. Hearts were exposed to 35 ml DNase I (70 U/ml) forat least 1 hour with manual recirculation. The organs were washed againwith 500 ml PBS for at least 24 hours.

B) Decellularisation Protocol #2 (Triton X and Trypsin)

Hearts were washed in 200 ml PBS containing 100 U/ml Penicillin, 0.1mg/ml Streptomycin, and 0.25 μg/ml Amphotericin B for at least about 20minutes with no recirculation. Hearts were then decellularized with0.05% Trypsin for 30 min followed by perfusion with 500 ml PBScontaining 5% Triton-X and 0.1% ammonium-hydroxide for about 6 hours.Hearts were perfused with deionized water for about 1 hour, and thenperfused with PBS for 12 h. Hearts were then washed 3 times for 24 hourseach time in 500 ml PBS using a pump for recirculation. The hearts wereperfused with 35 ml DNase I (70 U/ml) for 1 hour with manualrecirculation and washed twice in 500 ml PBS for at least about 24 hourseach time using a pump for recirculation.

C) Decellularization Protocol #3 (1% SDS)

Hearts were washed in 200 ml PBS containing 100 U/ml Penicillin, 0.1mg/ml Streptomycin, and 0.25 μg/ml Amphotericin B for at least about 20mins with no recirculation. The hearts were decellularized with 500 mlwater containing 1% SDS for at least about 6 hours using a pump forrecirculation. The hearts were then washed with deionized water forabout 1 hour and washed with PBS for about 12 hours. The hearts werewashed three times with 500 ml PBS for at least about 24 hours each timeusing a pump for recirculation. The heart was then perfused with 35 mlDNase I (70 U/ml) for about 1 hour using manual recirculation, andwashed three times with 500 ml PBS for at least about 24 hours each timeusing a pump for recirculation.

D) Decellularisation Protocol #4 (Triton X)

Hearts were washed with 200 ml PBS containing 100 U/ml Penicillin, 0.1mg/ml Streptomycin, and 0.25 μg/ml Amphotericin B for at least about 20mins with no recirculation. Hearts were then decellularized with 500 mlwater containing 5% Triton X and 0.1% ammonium hydroxide for at least 6hours using a pump for recirculation. Hearts were then perfused withdeionized water for about 1 hour and then with PBS for about 12 hours.Hearts were washed by perfusing with 500 ml PBS 3 times for at least 24hours each time using a pump for recirculation. Hearts were thenperfused with 35 ml DNase I (70 U/ml) for about 1 hour using manualrecirculation, and washed three times in 500 ml PBS for about 24 hourseach time.

For initial experiments, the decellularisation apparatus was set upwithin a laminar flow hood. Hearts were perfused at a coronary perfusionpressure of 60 cm H₂O. Although not required, the hearts described inthe experiments above were mounted in a decellularisation chamber andcompletely submerged and perfused with PBS containing antibiotics for 72hours in recirculation mode at a continuous flow of 5 ml/min to wash outas many cellular components and detergent as possible.

Successful decellularization was defined as the lack of myofilaments andnuclei in histologic sections. Successful preservation of vascularstructures was assessed by perfusion with 2% Evans Blue prior toembedding tissue sections.

Highly efficient decellularization took place when a heart was firstperfused antegradely with an ionic detergent (1% sodium-dodecyl-sulfate(SDS), approximately 0.03 M) dissolved in deionized H₂O at a constantcoronary perfusion pressure and then was perfused antegradely with anon-ionic detergent (1% Triton X-100) to remove the SDS and presumablyto renature the extracellular matrix (ECM) proteins. Intermittently, theheart was perfused retrogradely with phosphate buffered solution toclear obstructed capillaries and small vessels.

Example 5—Evaluation of Decellularized Organs

To demonstrate intact vascular structures following decellularization, adecellularized heart is stained via Langendorff perfusion with EvansBlue to stain vascular basement membrane and quantify macro- andmicro-vascular density. Further, polystyrene particles can be perfusedinto and through a heart to quantify coronary volume, the level ofvessel leakage, and to assess the distribution of perfusion by analyzingcoronary effluent and tissue sections. A combination of three criteriaare assessed and compared to isolated non-decellularised heart: 1) aneven distribution of polystyrene particles, 2) significant change inleakiness at some level 3) microvascular density.

Fiber orientation is assessed by the polarized-light microscopytechnique of Tower et al. (2002, Fiber alignment imaging duringmechanical testing of soft tissues, Ann Biomed Eng., 30(10):1221-33),which can be applied in real-time to a sample subjected to uniaxial orbiaxial stress. During Langendorff perfusion, basic mechanicalproperties of the decellularised ECM are recorded (compliance,elasticity, burst pressure) and compared to freshly isolated hearts.

Section B. Decellularization (Part II) Example 1—Decellularization ofRat Heart

Male 12 week old F344 Fischer rats (Harlan Labs, PO Box 29176Indianapolis, Ind. 46229), were anesthetized using intraperitonealinjection of 100 mg/kg ketamine (Phoenix Pharmaceutical, Inc., St.Joseph, Mo.) and 10 mg/kg xylazine (Phoenix Pharmaceutical, Inc., St.Joseph, Mo.). After systemic heparinization (American PharmaceuticalPartners, Inc., Schaumberg, Ill.) through the left femoral vein, amedian sternotomy was performed and the pericardium was opened. Theretrosternal fat body was removed, the ascending thoracic aorta wasdissected and its branches ligated. The caval and pulmonary veins, thepulmonary artery and the thoracic aorta were transsected and the heartwas removed from the chest. A prefilled 1.8 mm aortic canula (RadnotiGlass, Monrovia, Calif.) was inserted into the ascending aorta to allowretrograde coronary perfusion (Langendorff). The hearts were perfusedwith heparinized PBS (Hyclone, Logan, Utah) containing 10 μM adenosineat a coronary perfusion pressure of 75 cm H₂O for 15 minutes followed by1% sodium dodecyl sulfate (SDS) or 1% polyethylene glycol 1000 (PEG1000) (EMD Biosciences, La Jolla, Germany) or 1% Triton-X 100 (Sigma,St. Louis, Mo.) in deionized water for 2-15 hours. This was followed by15 minutes of deionized water perfusion and 30 minutes of perfusion with1% Triton-X (Sigma, St. Louis, Mo.) in deionized water. The hearts werethen continuously perfused with antibiotic-containing PBS (100 U/mlpenicillin-G (Gibco, Carlsbad, Calif.), 100 U/ml streptomycin (Gibco,Carlsbad, Calf.) and 0.25 μg/ml Amphotericin B (Sigma, St. Louis, Mo.))for 124 hours.

After 420 minutes of retrograde perfusion with either 1% PEG, 1%Triton-X 100 or 1% SDS, PEG and Triton-X 100 perfusion induced anedematous, opaque appearance, while SDS perfusion resulted in a moredramatic change leading to a nearly translucent graft as opaque elementswere slowly washed out. Hearts exposed to all three protocols remainedgrossly intact with no evidence of coronary rupture or aortic valveinsufficiency throughout the perfusion protocol (at constant coronaryperfusion pressure of 77.4 mmHg). Coronary flow decreased in all threeprotocols during the first 60 minutes of perfusion, then normalizedduring SDS perfusion while remaining increased in Triton-X 100 and PEGperfusion. SDS perfusion induced the highest initial increase incalculated coronary resistance (up to 250 mmHg·s·ml⁻¹), followed byTriton-X (up to 200 mmHg·s·ml⁻¹) and PEG (up to 150 mmHg·s·ml⁻¹).

Using histological sections of the detergent perfused heart tissue, itwas determined that decellularization over the observed time period wasincomplete in both PEG and Triton-X 100 treated hearts;Hematoxylin-Eosin (H&E) staining showed nuclei and cross-striatedfilaments. In contrast, no nuclei or contractile filaments weredetectable in sections of SDS-perfused hearts. Vascular structures andECM fiber direction, however, were preserved in the SDS-treated hearts.

To remove the ionic SDS from the ECM after the initialdecellularization, the organ was perfused for 30 minutes with Triton-X100. In addition and to ensure complete washout of all detergents and toreestablish a physiologic pH, the decellularized organ was perfusedextensively with deionized water and PBS for 124 h.

Example 2—Decellularization of Rat Kidney

For kidney isolation, the entire peritoneal content was wrapped in wetgauze and carefully mobilized to the side to expose the retroperitonealspace. The mesenteric vessels were ligated and transected. The abdominalaorta was ligated and transected below the take off of the renalarteries. The thoracic aorta was transected just above the diaphragm andcanulated using a 1.8 mm aortic canula (Radnoti Glass, Monrovia,Calif.). The kidneys were carefully removed from the retroperitoneum andsubmerged in sterile PBS (Hyclone, Logan, Utah) to minimize pullingforce on the renal arteries. 15 minutes of heparinized PBS perfusionwere followed by 2-16 hours of perfusion with 1% SDS (Invitrogen,Carlsbad, Calif.) in deionized water and 30 minutes of perfusion with 1%Triton-X (Sigma, St. Louis, Mo.) in deionized water. The liver was thencontinuously perfused with antibiotic containing PBS (100 U/mlpenicillin-G (Gibco, Carlsbad, Calif.), 100 U/ml streptomycin (Gibco,Carlsbad, Calif.), 0.25 μg/ml Amphotericin B (Sigma, St. Louis, Mo.))for 124 hours.

420 minutes of SDS perfusion followed by Triton-X 100 yielded acompletely decellularized renal ECM scaffold with intact vasculature andorgan architecture. Evans blue perfusion confirmed intact vasculaturesimilar to decellularized cardiac ECM. Movat pentachrome staining ofdecellularized renal cortex showed intact glomeruli and proximal anddistal convoluted tubule basement membranes without any intact cells ornuclei. Staining of decellularized renal medulla showed intact tubuleand collecting duct basement membranes. SEM of decellularized renalcortex confirmed intact glomerular and tubular basement membranes.Characteristic structures such as Bowman's capsule delineating theglomerulus from surrounding proximal and distal tubules and glomerularcapillary basement membranes within the glomeruli were preserved. SEMimages of decellularized renal medulla showed intact medullary pyramidsreaching into the renal pelvis with intact collecting duct basalmembranes leading towards the papilla. Thus, all the majorultrastructures of the kidney were intact after decellularization.

Example 3—Decellularization of Rat Lung

The lung (with the trachea) were carefully removed from the chest andsubmerged in sterile PBS (Hyclone, Logan, Utah) to minimize pullingforce on the pulmonary arteries. 15 minutes of heparinized PBS perfusionwas followed by 2-12 hours of perfusion with 1% SDS (Invitrogen,Carlsbad, Calif.) in deionized water and 15 minutes of perfusion with 1%Triton-X (Sigma, St. Louis, Mo.) in deionized water. The lung was thencontinuously perfused with antibiotic containing PBS (100 U/mlpenicillin-G (Gibco, Carlsbad, Calif.), 100 U/ml streptomycin (Gibco,Carlsbad, Calif.), 0.25 μg/ml Amphotericin B (Sigma, St. Louis, Mo.))for 124 hours.

180 minutes of SDS perfusion followed by Triton-X 100 perfusion yieldeda completely decellularized pulmonary ECM scaffold with intact airwaysand vessels. Movat pentachrome staining of histologic sections showedthe presence of ECM components in lung including major structuralproteins such as collagen and elastin and also soluble elements such asproteoglycans. However, no nuclei or intact cells were retained. Airwayswere preserved from the main bronchus to terminal bronchiole torespiratory bronchioles, alveolar ducts and alveoles. The vascular bedfrom pulmonary arteries down to the capillary level and pulmonary veinsremained intact. SEM micrographs of decellularized lung showed preservedbronchial, alveolar and vascular basement membranes with no evidence ofretained cells. The meshwork of elastic and reticular fibers providingthe major structural support to the interalveolar septum as well as theseptal basement membrane were intact, including the dense network ofcapillaries within the pulmonary interstitium.

SEM micrographs of the decellularized trachea showed intact ECMarchitecture with decellularized hyaline cartilage rings and a roughluminal basal membrane without respiratory epithelium.

Example 4—Decellularization of Rat Liver

For liver isolation, the caval vein was exposed through a medianlaparotomy, dissected and canulated using a mouse aortic canula (RadnotiGlass, Monrovia, Calif.). The hepatic artery and vein and the bile ductwere transsected and the liver was carefully removed from the abdomenand submerged in sterile PBS (Hyclone, Logan, Utah) to minimize pullingforce on portal vein. 15 minutes of heparinized PBS perfusion wasfollowed by 2-12 hours of perfusion with 1% SDS (Invitrogen, Carlsbad,Calif.) in deionized water and 15 minutes of 1% Triton-X (Sigma, St.Louis, Mo.) in deionized water. The liver was then continuously perfusedwith antibiotic containing PBS (100 U/ml penicillin-G (Gibco, Carlsbad,Calif.), 100 U/ml streptomycin (Gibco, Carlsbad, Calif.), 0.25 μg/mlAmphotericin B (Sigma, St. Louis, Mo.)) for 124 hours.

120 minutes of SDS perfusion followed by perfusion with Triton-X 100were sufficient to generate a completely decellularized liver. Movatpentachrome staining of decellularized liver confirmed retention ofcharacteristic hepatic organization with central vein and portal spacecontaining hepatic artery, bile duct and portal vein.

Example 5—Methods and Materials Used to Evaluate the DecellularizedOrgans

Histology and Immunofluorescence. Movat Pentachrome staining wasperformed on paraffin embedded decellularized tissues following themanufacturers instructions (American Mastertech Scientific, Lodi,Calif.). Briefly, deparaffinized slides were stained using Verhoeff'selastic stain, rinsed, differentiated in 2% ferric chloride, rinsed,placed in 5% sodium thiosulfate, rinsed, blocked in 3% glacial aceticacid, stained in 1% alcian blue solution, rinsed, stained in croceinscarlet—acid fuchsin, rinsed, dipped in 1% glacial acetic acid,destained in 5% phosphotungstic acid, dipped in 1% glacial acetic acid,dehydrated, placed in alcoholic saffron solution, dehydrated, mountedand covered.

Immunofluorescence staining was performed on decellularized tissues.Antigen retrieval was performed on paraffin-embedded tissue(recellularized tissue) but not on frozen sections (decellularizedtissue) as follows: Paraffin sections were de-waxed and rehydrated by 2changes of xylene for 5 minutes each, followed by sequential alcoholgradient and rinsing in cold running tap water. The slides were thenplaced in antigen retrieval solution (2.94 g tri-sodium citrate, 22 mlof 0.2 M hydrochloric acid solution, 978 ml ultra-pure water, andadjusted to a pH of 6.0) and boiled for 30 minutes. After rinsing underrunning cold tap water for 10 minutes, immunostaining was begun. Frozensections were fixed with 4% paraformaldehyde (Electron MicroscopySciences, Hatfield, Pa.) in 1×PBS (Mediatech, Herndon, Va.) for 15minutes at room temperature before staining. Slides were blocked with 4%Fetal Bovine Serum (FBS; HyClone, Logan, Utah) in 1×PBS for 30 minutesat room temperature. Samples were sequentially incubated for one hour atroom temperature with diluted primary and secondary antibodies (Ab).Between each step, slides were washed 3 times (5-10 min each) with1×PBS. Primary Ab against Collagen I (goat polyclonal IgG (Cat. No.sc-8788), Santa Cruz Biotechnology Inc., Santa Cruz, Calif.), CollagenIII (goat polyclonal IgG (Cat. No. sc-2405), Santa Cruz BiotechnologyInc., Santa Cruz, Calif.), Fibronectin (goat polyclonal IgG (Cat. No.sc-6953), Santa Cruz Biotechnology Inc., Santa Cruz, Calif.), andLaminin (rabbit polyclonal IgG (Cat. No. sc-20142), Santa CruzBiotechnology Inc., Santa Cruz, Calif.) were used at a 1:40 dilutionwith blocking buffer. Secondary Ab's bovine anti-goat IgG phycoerythin(Cat. No. sc-3747, Santa Cruz Biotechnology Inc., Santa Cruz, Calif.)and bovine anti-rabbit IgG phycoerythin (Cat. No. sc-3750, Santa CruzBiotechnology Inc., Santa Cruz, Calif.) were used at a 1:80 dilutionwith blocking buffer. Slides were covered with cover glass (Fisherbrand22×60, Pittsburgh, Pa.) in hardening mounting medium containing4′,6-diamidino-2-phenylindole (DAPI) (Vectashield, Vector Laboratories,Inc., Burlingame, Calif.). Images were recorded using ImagePro Plus4.5.1 (Mediacybernetics, Silver Spring, Md.) on a Nikon Eclipse TE200inverted microscope (Fryer Co. Inc., Huntley, Ill.) using ImagePro Plus4.5.1 (Mediacybernetics, Silver Spring, Md.).

Scanning Electron Microscopy. Normal and decellularized tissues wereperfusion fixed with 2.5% glutaraldehyde (Electron Microscopy Sciences,Hatfield, Pa.) in 0.1 M cacodylate buffer (Electron Microscopy Sciences,Hatfield, Pa.) for 15 minutes. Tissues were then rinsed two times in 0.1M cacodylate buffer for 15 minutes. Post-fixation was performed with 1%osmium tetroxide (Electron Microscopy Sciences, Hatfield, Pa.) for 60minutes. Tissue samples were then dehydrated in increasingconcentrations of EtOH (50% for 10 minutes, 70% for 10 minutes twotimes, 80% for 10 minutes, 95% for 10 minutes two times, 100% for 10minutes two times). Tissue samples then underwent critical point dryingin a Tousimis Samdri-780A (Tousimis, Rockville, Md.). Coating wasperformed with 30 seconds of Gold/Palladium sputter coating in theDenton DV-502A Vacuum Evaporator (Denton Vacuum, Moorestown, N.J.).Scanning electron microscopy images were taken using a Hitachi 54700Field Emission Scanning Electron Microscope (Hitachi High TechnologiesAmerica, Pleasanton, Calif.).

Mechanical Testing. Crosses of myocardial tissue were cut from the leftventricle of rats so that the center area was approximately 5 mm×5 mmand the axes of the cross were aligned in the circumferential andlongitudinal directions of the heart. The initial thickness of thetissue crosses were measured by a micrometer and found to be 3.59±0.14mm in the center of the tissue cross. Crosses were also cut fromdecellularized rat left ventricular tissue in the same orientation andwith the same center area size. The initial thickness of thedecellularized samples was 238.5±38.9 μm. In addition, the mechanicalproperties of fibrin gels was tested, another tissue engineeringscaffold used in engineering vascular and cardiac tissue. Fibrin gelswere cast into cross-shaped molds with a final concentration of 6.6 mgof fibrin/ml. The average thickness of the fibrin gels was 165.2±67.3μm. All samples were attached to a biaxial mechanical testing machine(Instron Corporation, Norwood, Mass.) via clamps, submerged in PBS, andstretched equibiaxially to 40% strain. In order to probe the staticpassive mechanical properties accurately, the samples were stretched inincrements of 4% strain and allowed to relax at each strain value for atleast 60 seconds. Forces were converted to engineering stress bynormalizing the force values with the cross sectional area in thespecific axis direction (5 mm×initial thickness). Engineering stress wascalculated as the displacement normalized by the initial length. Inorder to compare the data between the two axes as well as between samplegroups, a tangential modulus was calculated as follows:[T(∈=40% strain)−T(∈=36% strain)]/4% strainwhere T is engineering stress and ∈ is engineering strain. The valuesfor the tangential modulus were averaged and compared between the twoaxes (circumferential and longitudinal) as well as between groups.

Example 6—Assessment of Biocompatibility of Decellularized Organ

To assess biocompatibility, 100,000 mouse embryonic stem cells (mESC)suspended in 1 cc of standard expansion media (Iscove's ModifiedDulbecco's Medium (Gibco, Carlsbad, Calif.), 10% Fetal Bovine Serum(HyClone, Logan, Utah), 100 U/ml penicillin-G (Gibco, Carlsbad, Calif.),100 U/ml streptomycin (Gibco, Carlsbad, Calif.), 2 mmol/L L-glutamine(Invitrogen, Carlsbad, Calif.), 0.1 mmol/L 2-mercaptoethanol (Gibco,Carlsbad, Calif.) were seeded onto the ECM sections and on controlplates without specific growth factor stimulation or feeder cellsupport. 4′,6-Diamidino-2-phenylindole (DAPI) was added to the cellculture media at a concentration of 10 μg/ml to label cell nuclei and toallow quantification of cell attachment and expansion. Images wererecorded under UV-light and phase contrast at baseline, 24, 48 and 72hours thereafter using ImagePro Plus 4.5.1 (Mediacybernetics, SilverSpring, Md.) on a Nikon Eclipse TE200 inverted microscope (Fryer Co.Inc., Huntley, Ill.).

The decellularized ECM was compatible with cell viability, attachmentand proliferation. Seeded mESCs engrafted on the ECM scaffolds and beganto invade the matrix within 72 h of cell seeding.

Example 7—Evaluation of Decellularized Organs

Aortic valve competence and integrity of the coronary vascular bed ofSDS decellularized rat heart was assessed by Langendorff perfusion with2% Evans blue dye. No left ventricular filling with dye was observed,indicating an intact aortic valve. Macroscopically, filling of thecoronary arteries up to the fourth branching point was confirmed withoutsigns of dye leakage. In tissue sections, perfusion of large (150 μm)and small (20 μm) arteries and veins was subsequently confirmed by redfluorescence of Evans blue-stained vascular basal membrane.

To confirm the retention of major cardiac ECM components,immunofluorescent staining of SDS decellularized ECM scaffolds wasperformed. This confirmed the presence of major cardiac ECM componentssuch as collagens I and III, fibronectin and laminin, but showed noevidence of retained intact nuclei or contractile elements includingcardiac myosin heavy chain or sarcomeric alpha actin.

Scanning electron micrographs (SEM) of SDS decellularized cardiac ECMdemonstrated that fiber orientation and composition were preserved inaortic wall and aortic valve leaflet with an absence of cells throughoutthe entire tissue thickness. Decellularized left and right ventricularwall retained ECM fiber composition (weaves, struts, coils) andorientation, while myofibers were completely removed. Within theretained ECM of both ventricles, intact vascular basal membranes ofdifferent diameters without endothelial or smooth muscle cells wereobserved. Furthermore, a thin layer of dense epicardial fibersunderneath an intact epicardial basal lamina was retained.

To assess mechanical properties of decellularized heart tissue, bi-axialtesting was performed and compared to fibrin gels, which is frequentlyused as an artificial ECM scaffold in cardiac tissue engineering. Thenormal rat ventricle and decellularized samples were highly anisotropicwith respect to the stress-strain behavior. Conversely, in the fibringel sample, the stress-strain properties were extremely similar betweenthe two principal directions. The directional dependence ofstress-strain behavior was present in all samples in the normal ratventricle and decellularized groups, and the isotropic nature of thestress-strain properties was typical of all samples in the fibrin gelgroup.

In order to compare the stress-strain properties between these twogroups and also between the principal axes of the hearts, a tangentialmodulus was calculated at 40% strain (see Example 5 for the equation) inboth the circumferential and longitudinal direction. Note that in bothdirections, the decellularized sample group had a significantly highermodulus than the normal rat ventricle and fibrin gel sample groups.There was a significant difference, however, between the moduli in thetwo directions for both the normal rat ventricle and the decellularizedmatrix, but not for the fibrin gel.

For the intact left ventricular tissue, the stress at 40% strain variedbetween 5 and 14 kPa in the longitudinal direction and between 15 and 24kPa in the circumferential direction, which is in agreement withpreviously published data. In both the rat ventricular tissue and thedecellularized rat ventricular tissue, the circumferential direction wasstiffer than the longitudinal direction, most likely due to muscle fiberorientation of the heart. While the fiber orientation changes throughthe thickness of the cardiac tissue, the majority of the fibers wereoriented in the circumferential direction and thus, this direction wouldbe expected to be stiffer. The decellularized tissue was significantlystiffer than the intact tissue. This also would be expected since theextracellular matrix is stiffer than the cells themselves, and thecombination of ECM and cells would likely not be as stiff as just theECM alone. While the values of the tangential modulus of thedecellularized tissue seem rather large, they are only slightly greaterthan values of the Young's modulus for purified elastin (approximately600 kPa) and less than Young's modulus of a single collagen fiber (5Mpa), placing the values determined herein within a reasonable range.

Example 8—Decellularization of Other Organs or Tissues

In addition to rat heart, lung, kidney and liver, similar results weregenerated by applying the perfusion decellularization protocol describedherein to skeletal muscle, pancreas, small and large bowel, esophagus,stomach, spleen, brain, spinal cord and bone.

Example 9—Decellularization of Pig Kidney

Pig kidneys were isolated from heparinized male animals. To allowperfusion of the isolated organs, the renal artery was emulated andblood was washed out with PBS perfusion over 15 minutes. Perfusion with27 L of 1% SDS in deionized water was performed for 35.5 hours at apressure of 50-100 mmHg. Perfusion with 1% Triton-X in deionized waterwas initiated to remove SDS from the ECM scaffold. Washing and bufferingof the decellularized kidneys was then performed by perfusion withantibiotic containing PBS for 120 hours to remove detergents and obtaina biocompatible pH.

Organ clearing was observed within two hours of initiating perfusion.Clear white color predominated 12 hours into perfusion.Decellularization was terminated with the organ was whitesemi-transparent.

Example 10—Transplantation of Decellularized Heart

Hearts from F344 rats were prepared by cannulating the aorta distal tothe Ao valve and ligating all other great vessels and pulmonary vesselsexcept the left branch of the pulmonary trunk (distal to itsbifurcation) and the inferior vena cava (WC). Decellularization wasachieved using Langendorf retrograde coronary perfusion and 2 liters of1% SDS over 12-16 hours. The hearts were then renatured with 35 mL of 1%Triton-X over 30-40 minutes, and then washed with antibiotic andantifungal-containing PBS for 72 hours. The IVC was ligated before thetransplantation.

A large (380 to 400 gram) RNU rat was prepared for reception of thedecellularized heart. A blunt-angled mosquito clamp was applied to boththe WC and the abdominal Ao of the host animal to ensure isolation ofareas of anastomosis. The aorta of the decellularized heart wasanastomosed to the host abdominal aorta proximal and inferior to therenal branches using 8-0 silk suture. The left branch of thedecellularized heart's pulmonary trunk was anastomosed to the closestregion of the host IVC to minimize physical stress on pulmonary trunk.

After both vessels were sewn into the host animal, the clamp wasreleased and the decellularized heart filled with the host animal'sblood. The recipient animal's abdominal aortic pressure was observedvisually in the decellularized heart and aorta. The decellularized heartbecame distended and red with blood. Bleeding was minimal at the site ofanastomosis. Heparin was administered 3 minutes after clamp release(initiation of perfusion), and the heart was photographed and positionedin the abdomen to minimize stress on the sites of anastomosis. Theabdomen was closed in sterile fashion and the animal monitored forrecovery. At 55 hours post-transplant, the animal was euthanized and thedecellularized heart was explanted for observation. The animals that didnot receive heparin showed a large thrombosis in the LV upon dissectionand evaluation. Blood was also observed in coronary arteries in both theright and left sides of the heart.

In other transplant experiments, the clamp was released after bothvessels were sewn into the host animal, and the decellularized heartfilled with the host animal's blood. The recipient animal's abdominalaortic pressure was observed visually in the decellularized heart andaorta. The decellularized heart became distended and red, and bleedingwas minimal at the site of anastomosis. Heparin was administered (3000IU) by IP injection 3 minutes after clamp release (initiation ofperfusion). The heart was photographed and positioned in the abdomen tominimize stress on the sites of anastomosis. The abdomen was closed insterile fashion and the animal monitored for recovery. The animal wasfound dead from hemorrhage at approximately 48 hours aftertransplantation. Transplantation time is currently in the 55 to 70minute range.

Section C. Recellularization Example 1—Recellularization of Cardiac ECMSlices

To evaluate biocompatibility of decellularised ECM, 1 mm thick slices ofone decellularised heart were cultured with myogenic and endothelialcell lines. 2×10⁵ rat skeletal myoblasts, C2C12 mouse myoblasts, humanumbilical cord endothelial cells (HUVECs), and bovine pulmonaryendothelial cells (BPEC) were seeded onto tissue sections andco-cultured under standard conditions for 7 days. Myogenic cellsmigrated through and expanded within the ECM and aligned with theoriginal fiber orientation. These myogenic cells showed increasedproliferation and fully re-populated large portions of the ECM slice.Endothelial cell lines showed a less invasive growth pattern, forming amonolayer on the graft surface. There were no detectableantiproliferative effects under these conditions.

Example 2—Recellularisation of Cardiac ECM by Coronary Perfusion

To determine the efficiency of seeding regenerative cells onto and intodecellularised cardiac ECM by coronary perfusion, a decellularized heartwas transferred to an organ chamber and continuously perfused withoxygenised cell culture media under cell culture conditions (5% CO₂, 60%humiditiy, 37° C.). 120×10⁶ PKH labelled HUVECs (suspended in 50 ml ofendothelial cell growth media) were infused at 40 cm H₂O coronaryperfusion pressure. Coronary effluent was saved and cells were counted.The effluent was then recirculated and perfused again to deliver amaximum number of cells. Recirculation was repeated two times. After thethird passage, approximately 90×10⁶ cells were retained within theheart. The heart was continuously perfused with 500 ml of recirculatingoxygenised endothelial cell culture media for 120 hours. The heart wasthen removed and embedded for cryosectioning. HUVECs were confined toarterial and venous residues throughout the heart, but were not yetcompletely dispersed throughout the extravascular ECM.

Example 3—Recellularization of a Decellularized Rat Heart with NeonatalRat Heart Cells

Isolation and preparation of rat neonatal cardiocytes. On day one, eightto ten SPF Fisher-344 neonatal pups, aged 1-3 days (Harlan Labs,Indianapolis, Ind.), were sedated with 5% inhaled Isoflurane (AbbottLaboratories, North Chicago, Ill.), sprayed with 70% EtOH, and a rapidsternotomy was performed in sterile fashion. Hearts were excised andplaced immediately into 50 ml conical tube on ice containing HBSS;Reagent #1 from a neonatal cardiomyocyte isolation system (WorthingtonBiochemical Corporation, Lakewood, N.J.).

Supernatant was removed and whole hearts were washed once with cold HBSSby vigorous swirling. Hearts were transferred to a 100 mm culture dishcontaining 5 ml cold HBSS, the connective tissue was removed, andremaining tissue was minced into pieces <1 mm². Additional HBSS wasadded to bring total plate volume to 9 ml, to which 1 ml Trypsin(Reagent #2, Worthington kit) was added to give a final concentration of50 μg/ml. Plates were incubated overnight in a 5° C. cooler.

On day two, the plates were removed from the cooler and placed in asterile hood on ice. Tissue and trypsin-containing buffer weretransferred to 50 ml conical tubes on ice using wide-mouth pipettes.Trypsin Inhibitor (Reagent #3) was reconstituted with 1 ml HBSS (Reagent#1) and added to the 50 ml conical tube and gently mixed. The tissue wasoxygenated for 60-90 seconds by passing air over the surface of theliquid. The tissue was then warmed to 37° C. and collagenase (300units/ml) reconstituted with 5 ml Leibovitz L-15 was added slowly. Thetissue was placed in a warn (37° C.) shaker bath for 45 minutes. Next,the tissue was titrated ten times using a 10 ml pipet to release thecells (3 mis per second) and then strained through a 0.22 μm filter. Thetissue was washed with an 5 additional mis of L-15 media, titrated asecond time, and collected in the same 50 ml conical tube. The solutionof cells was then incubated at room temperature for 20 minutes, and spunat 50×g for five minutes to pellet the cells. The supernatant was gentlyremoved and the cells were resuspended in the desired volume usingNeonatal-Cardiomyocyte Media.

Media and Solutions. All media were sterile filtered and stored in thedark in 5° C. coolers. Worthington Isolation Kit contains a suggestedmedia, Leibovitz L-15, for culture. This media was used for Day Two ofthe tissue processing only. For plating, an alternate calcium-containingmedia was used, which is described herein. Worthington Leibovitz L-15Media: Leibovitz media powder was reconstituted using 1 L cell-culturegrade water. Leibovitz L-15 media contains 140 mg/ml CaCl, 93.68 mg/mlMgCl, and 97.67 mg/ml MgS. Neonatal-Cardiomyocyte Media: Iscove'sModified Dulbecco's Medium (Gibco, Cat. No. 12440-053) was supplementedwith 10% Fetal Bovine Serum (HyClone), 100 U/ml penicillin-G (Gibco),100 U/ml streptomycin (Gibco), 2 mmol/L L-glutamine (Invitrogen), and0.1 mmol/L 2-mercaptoethanol (Gibco, Cat. No. 21985-023) and sterilefiltered before use. Amphotericine-B was added as needed (0.25 μg/mlfinal concentration). This media was enhanced with 1.2 mM CaCl (FisherScientific, Cat. No. C614-500) and 0.8 mM MgCl (Sigma, Cat. No. M-0250).

In Vitro Culture Analysis of Recellularization. As a step towardscreating a bioartificial heart, the isolated ECM was recellularized withneonatal heart-derived cells. Completely decellularized hearts (made asdescribed herein) were injected with a combination of 50×10⁶ freshlyisolated rat neonatal cardiomyocytes, fibrocytes, endothelial and smoothmuscle cells. The heart tissue was then sliced and the slices werecultured in vitro to test the biocompatibility of the decellularized ECMand the ability of the resulting constructs to develop into myocardiumrings.

Minimal contractions within the resulting rings were observedmicroscopically after 24 hours, demonstrating that the transplantedcells were able to attach and engraft on the decellularized ECM.Microscopically, cells oriented along the ECM fiber direction.Immunofluorescence staining confirmed the survival and engraftment ofcardiomyocytes expressing cardiac myosin heavy chain. Within four days,clusters of contracting cell patches were observed on the decellularizedmatrix, which progressed to synchronously contracting tissue rings byday 8.

At day 10, these rings were mounted between two rods to measurecontractile force under different preload conditions. The rings could beelectrically paced up to a frequency of 4 Hz and created contractileforce of up to 3 mN under a preload of up to 0.65 g. Thus, with this invitro tissue culture approach of recellularization, contractile tissuewas obtained that generated an equally effective force as that generatedby optimized engineered heart tissue rings using artificial ECMconstructs.

Recellularization of a Decellularized Heart via Perfusion.Recellularized (50×10⁶ freshly isolated rat neonatal cardiomyocytes,fibrocytes, endothelial and smooth muscle cells) scaffolds were mountedin a perfusable bioreactor (n=10) that simulated rat cardiac physiologyincluding pulsatile left ventricular distension with graduallyincreasing preload and afterload (day 1: preload 4-12 mmHg, afterload3-7 mmHg), pulsatile coronary flow (day 1: 7 ml/min), and electricstimulation (day 2: 1 Hz) under sterile cardiac tissue cultureconditions (5% CO₂, 60% H₂O, 37° C.). Perfused organ culture wasmaintained for one to four weeks. Pressures, flows and EKG were recordedfor 30 seconds every 15 minutes throughout the entire culture period.Videos of the nascent bioartificial hearts were recorded at days four,six and ten after cell seeding.

At day 10 after cell seeding, a more in-depth functional assessment wasperformed including insertion of a pressure probe into the leftventricle to record left ventricular pressure (LVP) and video recordingof wall motion as the stimulation frequency was gradually increased from0.1 Hz to 10 Hz and performed pharmacological stimulation withphenylephrine (PE). The recellularized heart showed contractile responseto single paces with spontaneous contractions following the pacedcontractions with corresponding increases in LVP. After a single pace,the heart showed three spontaneous contractions and then converted to afibrillatory state. Similar to the stimulated contractions, spontaneousdepolarizations caused a corresponding increase in LVP and a recordableQRS complex possibly indicating the formation of a developing stableconduction pattern.

Once stimulation frequency was increased to 0.4 Hz, an average of twospontaneous contractions occurred after each induced contraction; at apacing frequency up to 1 Hz, only one spontaneous contraction occurred;and at a pacing frequency of 5 Hz, no spontaneous contractions occurred.Maximum capture rate was 5 Hz, which is consistent with a refractoryperiod of 250 ms for mature myocardium. After perfusion with 100 μM ofPE, regular spontaneous depolarizations occurred at a frequency of 1.7Hz and were coupled with corresponding increases in LVP.

Histological analysis at day 10 revealed cell dispersion and engraftmentthroughout the entire thickness of the left ventricular wall (0.5-1.2mm) Cardiomyocytes aligned with the ventricular fiber direction andformed areas of dense, organized grafts resembling mature myocardium andless dense immature grafts similar to developing myocardium.Immunofluorescence staining for cardiac myosin heavy chain confirmed thecardiomyocyte phenotype. A high capillary density was maintainedthroughout the newly developed myocardium with an average distancebetween capillaries of approximately 20 μm, which is similar to thatreported for mature rat myocardium. Endothelial cell phenotype wasconfirmed by immunofluorescent staining for vonWillebrand Factor (vWF).Cell viability was maintained throughout the entire graft thickness,indicating sufficient oxygen and nutrient supply through coronaryperfusion.

OTHER EMBODIMENTS

It is to be understood that while the invention has been described inconjunction with the detailed description thereof, the foregoingdescription is intended to illustrate and not limit the scope of theinvention, which is defined by the scope of the appended claims. Otheraspects, advantages, and modifications are within the scope of thefollowing claims.

What is claimed is:
 1. A perfusion decellularized extracellular matrixportion of a pig, bovine, sheep, or canine organ comprising anon-vasculature decellularized extracellular matrix and vasculaturedecellularized extracellular matrix, wherein said vasculaturedecellularized extracellular matrix retains a majority of fluidintroduced to said vasculature decellularized extracellular matrix,wherein said vascular decellularized extracellular matrix compriseshuman cells, wherein said organ is a kidney, lung, liver, pancreas, orspleen, and wherein prior to decellularization the perfusiondecellularized extracellular matrix portion included about 10,000,000cells/mg tissue or wherein the perfusion decellularized extracellularmatrix portion is capable of being reseeded with at least 10,000,000cells.
 2. A perfusion decellularized solid organ of a pig, bovine,sheep, or canine comprising a non-vasculature decellularizedextracellular matrix and vasculature decellularized extracellularmatrix, wherein said vasculature decellularized extracellular matrixretains a majority of fluid introduced to said vasculaturedecellularized extracellular matrix, wherein said vasculardecellularized extracellular matrix comprises human cells, wherein saidperfusion decellularized solid organ is a kidney, lung, liver, pancreas,or spleen, and wherein prior to decellularization a perfusiondecellularized portion included about 10,000,000 cells/mg tissue orwherein the perfusion decellularized solid organ is capable of beingreseeded with at least 10,000,000 cells.
 3. The perfusion decellularizedextracellular matrix portion of claim 1, wherein said human cells areregenerative cells.
 4. The perfusion decellularized extracellular matrixportion of claim 1, wherein said human cells are autologous to apatient.
 5. The perfusion decellularized extracellular matrix portion ofclaim 1, wherein said human cells are allogenic to a patient.
 6. Theperfusion decellularized extracellular matrix portion of claim 1,wherein said human cells are progenitor cells.
 7. The perfusiondecellularized extracellular matrix portion of claim 1, wherein saidhuman cells are stem cells.
 8. The perfusion decellularized solid organof claim 2, wherein said human cells are regenerative cells.
 9. Theperfusion decellularized solid organ of claim 2, wherein said humancells are autologous to a patient.
 10. The perfusion decellularizedsolid organ of claim 2, wherein said human cells are allogenic to apatient.
 11. The perfusion decellularized solid organ of claim 2,wherein said human cells are progenitor cells.
 12. The perfusiondecellularized solid organ of claim 2, wherein said human cells are stemcells.
 13. A perfusion decellularized solid organ or portion thereof ofa pig, bovine, sheep, or canine comprising a cannula, non-vasculaturedecellularized extracellular matrix, and vasculature decellularizedextracellular matrix, wherein said vasculature decellularizedextracellular matrix retains a majority of fluid introduced to saidvasculature decellularized extracellular matrix, wherein said vasculardecellularized extracellular matrix comprises cells, wherein saidperfusion decellularized solid organ or portion thereof is a kidney,lung, liver, pancreas, or spleen, and wherein prior to decellularizationa perfusion decellularized portion included about 10,000,000 cells/mgtissue or wherein the perfusion decellularized solid organ or portionthereof is capable of being reseeded with at least 10,000,000 cells. 14.The perfusion decellularized solid organ or portion thereof of claim 13,wherein said cells are regenerative cells.
 15. The perfusiondecellularized solid organ or portion thereof of claim 13, wherein saidcells are autologous to a patient.
 16. The perfusion decellularizedsolid organ or portion thereof of claim 13, wherein said cells areallogenic to a patient.
 17. The perfusion decellularized solid organ orportion thereof of claim 13, wherein said cells are progenitor cells.18. The perfusion decellularized solid organ or portion thereof of claim13, wherein said cells are stem cells.
 19. The perfusion decellularizedextracellular matrix portion of claim 1, wherein the pre-perfusiondecellularized extracellular matrix portion prior to decellularizationincluded about 10,000,000 cells/mg tissue.
 20. The perfusiondecellularized extracellular matrix portion of claim 1, wherein thedecellularized extracellular matrix portion is capable of being reseededwith at least 10,000,000 cells.
 21. The perfusion decellularized solidorgan of claim 2, wherein the portion of the pre-perfusiondecellularized solid organ prior to decellularization included about10,000,000 cells/mg tissue.
 22. The perfusion decellularized solid organof claim 2, wherein the perfusion decellularized solid organ is capableof being reseeded with at least 10,000,000 cells.
 23. The perfusiondecellularized solid organ or portion thereof of claim 13, wherein theportion of a pre-perfusion decellularized solid organ included about10,000,000 cells/mg tissue.
 24. The perfusion decellularized solid organor portion thereof of claim 13, wherein the perfusion decellularizedsolid organ or portion is capable of being reseeded with at least10,000,000 cells.
 25. The perfusion decellularized solid organ orportion thereof of claim 13, wherein the perfusion decellularized solidorgan or portion is a solid organ.
 26. The perfusion decellularizedsolid organ or portion thereof of claim 13, wherein the perfusiondecellularized solid organ or portion is a portion of the solid organ.